Device for filtering ECG signals

Abstract: A device for filtering ECG signals, comprises an A/D converter (12) and a filter unit (14) connected to the converter's output. The filter unit comprises a filter, or a combination of filters with such a non-linear phase response that signals with frequencies in the passband of the filter, or the combination of filters, are delayed more than signals with frequencies in the transition band between the passband and the suppressed frequency band of the filter, or the combination of filters. A method for producing a FIR filter, with a phase response opposite to the phase response of a filter for filtering out DC components or an IIR filter, suitable for use in the above-described device in which the impulse response from the said filter (10) for filtering out DC components and low-frequency components or said IIR filter is reversed in time and sampled. The sampled values are then used for determining coefficients for the FIR filter.

Description: This invention relates to a device for filtering ECG signals, comprising an A/D converter for converting analog input signals to a series of digital values, corresponding to the input signals at different times, and a filter unit connected to the A/D converter's output, said filter unit comprising a filter, or a combination of filters, with such a non-linear phase response, that signals with frequencies in the passband of the filter, or the combination of filters, are delayed more than signals with frequencies in the transition band between the passband and the suppressed frequency band of the filter, or the combination of filters. A device of this kind is previously known from WO-93/05573. Filtration of the signals is required for the analysis of ECG signals. The ECG signal recorded between two electrodes on the patient's body, e.g. on the arms and legs, also contains a DC potential, in addition to the ECG signal, which may be much larger than the ECG signal. These DC potentials or low-frequency signals vary because of relative movements of the body and the electrode as a result of e.g. the patient's breathing movements. Two-pass filtering is one way to remove these DC signals and low-frequency signals from the ECG signal. A filter with a linear phase is then provided by both forward and backward filtration of the signal with a filter with a non-linear phase, see e.g. GB patent 1 556 512, which describes this filtration with analog filters. A linear phase is desirable at the filtration, since phase distortion is then eliminated and, with that a minor distortion of the ECG signal's morphology results. However, a method in which the signal must be fed to the filter both in the forward and the back direction cannot straight off be used continuously, which is a major disadvantage when on-line filtering is desired in ECG examination lasting a longer time. The presence of high-frequency signals with small amplitudes on the microvolt level at the end of the QRS complex in post-infarction patients has been shown to be a good indication of an increased risk of future life-menacing ventricular arrhythmias, see. European Heart Journal (1991), 12, pp. 473 - 480. High-pass filtration is needed in order to identify and analyze these late potentials. One problem is then the ringing induced by the QRS signal itself and which readily drowns out any late potentials. Several proposals to solutions of this problem have been presented. In Link and Trahms, "Highpass Filters for Detecting Late Potentials", Proc. Computers in Cardiology 1992, pp. 159 - 162, the use of a non-recursive, monotone, binomial high-pass filter for detecting late potentials is proposed. In US patent 4 422 459 is described a technic for disclosing the presence or absence of a time segment containing high-frequency signals in the latter part of a patient's QRS complex and for measuring the magnitude of this segment. The measured analog ECG signals are then converted into digital signals, and normal QRS signals are averaged over some hundred beats in order to obtain a relatively noiseless complex. The latter part of the average values of the signals is then subjected to backward high-pass filtration so the ringings, which would otherwise occur after the QRS complex, are avoided. The disadvantage of this technic is the complexity of backward filtering. In US patent 4 458 691 is described a system for high-pass forward filtration of ECG signals for detection of late potentials, an adaptive high-pass filter for selective filtration of different segments of the QRS complex being used to solve the problem of ringing. This technic also has several disadvantages. Ringing is thus not completely eliminated, and to reduce the ringing effekt as much as possible short FIR filters with a linear phase are used, yielding poorer frequency splitting. In US patent 4 458 692 is described another method for detecting late potential through forward filtration of the ECG signal, regulation of filter gain depending on the magnitude of the input signal then being employed in trying to solve the problem of ringing. The signal controlling the gain can be the output signal from a filter using the QRS signal as input signal, and e.g the R spike's impact on the output signal and, thus, on the ringing occurring after the R spike, can be limited if the gain in the filter is limited when the input signal rises above a defined level. This method also has the disadvantage of failing to eliminate all ringings, and a steep filter slope must be sacrificed. US patent 4 492 235 also relates to detection of late potentials through forward filtration of the QRS signal, an adaptive high-pass filtration being employed to overcome the problems of ringing. In US patent 5 025 794 is described a further method for forward filtration of late potentials in which sampled values of the QRS signal are subjected to both forward and backward filtration, whereupon the filtered signals are added together and the summation signal is smoothed to yield signal components corresponding to the late potentials. The method described in this patent is complicated. The object of the present invention is to provide a device for the filtration of ECG signals in which the above-described disadvantages of the prior art are eliminated. This object is achieved with a device of the kind described in the introductory part with the characterizing features set forth in claim 1. In a device according to the invention, the filter thus has a non-linear phase response with "abnormal" phase properties. A normal high-pass filter with a non-linear phase response delays the signal in the transition band, between the suppressed frequency band and the pass band, more than the signal in the high-frequency passband. However, the filter in the device according to the invention is devised so the signal in the passband is delayed more than the signal in the transition band. In the device according to the invention, the filtration can also be performed in a combination of filters with the above mentioned property. With the device according to the invention, a.o. baseline filtration and detection of late potentials, are thus possible in a simple manner through forward filtration of the ECG signal. However, the filtration device can also be advantageously used for form classification of the ECG complex, ST measurements and delimitation of the ECG complex. According to advantageous refinements of the device according to the invention, a filter, such as an RC circuit, is disposed before the A/D converter to filter out DC and low-frequency components in the ECG signal, and the filter unit comprises a assymmetrical FIR filter with a phase response opposite to the phase response of said filter for filtering out DC and low-frequency components. If the baseline filtration is performed with a filter with a linear phase, the lower cut-off frequency can be chosen very close to the repetition frequency of the QRS complex, i.e. the heart's pulse rate. Because of phase distortion in an AC circuit, the cut-off frequency must be about tenfold lower to prevent excessive measurement errors. With the device according to the invention, therefore, suppression of the low-frequency fault signals, occurring when a patient moves during e.g. an exercise ECG, can be greatly improved by raising 10 times the cut-off frequency of the high-pass filter. Conventional backward filtration is not possible when ECG recording during an exercise test lasts for about 15 minutes. Another object of the present invention is to propose a method of the kind stated in the introductory part for producing a FIR filter suitable for use in the device according to the invention. This object is achieved with a method set forth in claim 10. With the method according to the invention, it is thus possible to construct a FIR filter whose output in forward filtration is virtually identical to the output signal from e.g. a corresponding IIR filter in backward filtration. It was feared that the use of such a FIR filter would require extensive calculations, however, to our surprise, we found that the calculations do not have to be performed with very great precision, so the analysis time is not prolonged by the calculations. One embodiment of the device according to the invention, chosen as an example, will now be described in greater detail with reference to the enclosed drawing in which FIG. 1 shows an equipment for recording ECG's with the device according to the invention; FIG. 2 shows a recorded ECG signal with a large superimposed DC component; FIG. 3 shows the ECG signal in FIG. 2 with the DC component filtered out; FIGS. 4 and 5 show the amplitude and phase characteristic of a high-pass filter in which the signal in the suppressed frequency band is delayed more than signal in the passband; FIG. 6 shows the impulse response for a filter, and FIG. 7 illustrates the sampling of this impulse response, reversed in time, for determining the coefficients for a FIR filter with the desired characteristic. An ECG is measured as the potential between electrodes on the patient's 2 body, e.g. on her/his arms 4 and legs 6, see FIG 1. The measured signals are supplied to an amplifier 8. The difference in the potential measured between two electrodes on the patient 2 also contains a DC potential, in addition to the ECG signal, which may be much larger than the ECG signal itself, see. FIG. 2. So, FIG. 2 shows the ECG signal as recorded. The ECG signal itself consists of minor variations on a large voltage. This large DC voltage also varies with the movements of the body and the electrodes, so elimination of this voltage from the recorded signal is desirable. One way of achieving this is to provide the input electronics 10 of the A/D converter 12 with a time constant, i.e. to AC couple them. With an RC coupling, the DC component in the recorded signal is therefore filtered out, cf FIG. 3, and the ECG can be measured around the zero line. A recording window can thus be placed around the zero line. The dynamic area will then be much smaller, and resolution requirements for the A/D conversion are reduced from 17 bits to 12 bits. However, such filtration with associated non-linear phase shift has major disadvantages for the subsequent processing of the ECG signal. The signal distortion occurring depends mainly on the fact that the signal in the suppression frequency band is delayed more than the signal in the passband. A major improvement would be achieved if the filtration could be performed with a linear phase, all signal frequencies then being delayed to an equal degree. The signals are therefore filtered in an additional filter 14 which has the same phase response, with opposite sign compared to the RC circuit. Such a filter 14 can be appropriately realized in the form of a digital filter, so the analog measurement signals are converted in the A/D converter 12 into a series of digital values, corresponding to the signal value at periodic times and supplied to the digital filter 14. The amplitude and phase characteristic of the RC circuit are illustrated in FIGS. 4 and 5. The impulse response of the RC circuit is the starting point in constructing a filter 14 which delays the signal in the passband more than the signal in the suppressed frequency band according to the above, see FIG. 6. The impulse response is reversed in time and sampled, and the sampled values are then employed as coefficients for an assymmetrical FIR filter. This is illustrated in FIG. 7 in which each sampled value forming a coefficient for the FIR filter 14 has been marked with an x. The RC filter for filtering out DC and low-frequency components is a hardware filter for which the filter unit subsequently shall compensate. The filter unit then shall have the same amplitude characteristic as the hardware filter, whereas its phase characteristic shall be the same, although with the opposite sign. The filter 14 can also be realized as a combination of filters, the filter combination then having the aforementioned characteristic. After the ECG signal has been filtered in this filter 14, all signal frequencies will be delayed to about the same degree and the signal is suitable for continued processing. Amplitude characteristic for the combined filtration corresponds to the characteristic of a cascade coupling of both the filters 10, 14, and the result of the combined filtration corresponds to the result which would be achieved if forward and backward filtration was performed with the RC-circuit. With the device shown in FIG. 1, two-pass filtering is thus realized without any need for backward filtration of the signal with the disadvantages such a method would entail, as discussed above. If baseline filtering is performed with a filter with a linear phase, the lower cut-off frequency can be chosen very close to the repetition frequency of the QRS complex, i.e. close to the heart's pulse rate. As a result of phase distortion in an RC circuit, the cut-off frequency must be set 10 times lower to prevent excessively large measurement errors. With the above-described device according to the invention, the suppression of the low-frequency fault signals occurring when a patient moves, e.g. during an exercise ECG, could be greatly improved if the cut-off frequency for the high-pass filter could be increased tenfold. Conventional backward filtration is then not possible as an ECG is recorded during an exercise test lasting about 15 minutes. One embodiment of the device according to the invention was described above for baseline filtration. However, the device according to the invention is suitable for a plurality of other applications. A device of the above-described kind is thus also very suitable for the detection of late potentials without any need for backward filtration in order to overcome the problem of ringing. The first part of the QRS complex is then first filtered in an IIR filter, whereupon the latter part of the complex and the signal a defined period of time thereafter are filtered in an assymmetrical FIR filter constructed in a manner analogous to the construction of the above-described filter for baseline filtration, i.e. the impulse response from the IIR filter is reversed in time and sampled, and the sampled values are then employed as coefficients for the FIR filter. The IIR filter's impulse response is infinite which would therefore yield an infinite number of coefficients in the FIR filter. However, the impulse response normally subsides so rapidly that a good approximation of the impulse response is achieved if the sequence of coefficients is cut off at a manageable, finite number. With the device according to the invention, the problems of ringing and phase distortion are consequently eliminated at the filtration of ECG signals with no need to perform backward filtration of the signals or parts thereof. The device according to the invention is also useful for form classification of ECG complexes, ST measurements of ECG complexes and delimitation of the ECG complex, as mentioned above. ST measurements relate to measurements made in the interval between the S in the QRS complex and the T wave. Interesting information can be found there, and measurements have been performed in this interval for a long time. Baseline filtration is then especially critical in exercise tests. The ST interval is a plateau, so correct reproduction of low frequencies is essential for this plateau to appear. As mentioned, forward-backward filtration has long been employed for baseline filtration, and this method has been common in conjunction with ST measurements. With the present invention, also this measurement is therefore greatly simplified.

Claims: Device for filtering ECG signals, comprising an A/D converter (12) for converting analog input signals to a series of digital values, corresponding to input signals at different times, and a filter unit (14) connected to the A/D converter's output, said filter unit comprising a filter (14), or a combination of filters, with such a non-linear phase response, that signals with frequencies in the passband of the filter, or the combination of filters, are delayed more than signals with frequencies in the transition band between the passband and the suppressed frequency band of the filter, or the combination of filters, characterized in that the filter unit comprises a high-pass filter (14), or a combination of filters, which forms a high-pass filter, in that a filter (10) is arranged to filter out the DC and low-frequency components in the ECG signal, and in that said high-pass filter (14), or said corresponding combination of filters, of the filter unit displays corresponding amplitude characteristic as said filter (10) for filtering out DC and low-frequency components and a phase response opposite to the phase response of the latter filter. Device according to claim 1, characterized in that the A/D converter (12) is devised to convert the analog input signal into a series of digital values corresponding to the input signal values at different periodic times. Device according to claim 1 or 2, characterized in that the filter (10) for filtering out DC and low-frequency components in the ECG signal comprises a hardware filter, preferably a RC circuit, disposed before the A/D converter (12), and in that said high-pass filter of the filter unit (14), or said combination of filters, display an amplitude characteristic corresponding to that of the hardware and a phase response opposite to the phase response of the hardware filter. Device according to any of claims 1 - 3, characterized in that the cut-off frequency of the high-pass filter (14) is lower than the repetition frequency of the studied QRS pattern. Device according to any of claims 1 - 4, characterized in that the high-pass filter of the filter unit (14), or said combination of filters, are realized with an asymmetrical high-pass FIR filter. Device according to claim 1 intended for identifying late potentials, characterized in that the A/D converter (12) is devised to convert the latter part of the QRS signal and a part of the analog input signal thereafter into digital values for subsequent filtration. Device according to claim 6, characterized in that the high-pass filter unit (14) is devised such that its amplitude characteristic corresponds to that of an IIR filter and its phase characteristic corresponds to the phase characteristic, with a reversed sign, of the same IIR filter. Device according to claim 5 or 7, characterized in that the FIR filter has coefficients, determined from sampled values of the impulse response, reversed in time, from said filter (10) for filtering out DC and low-frequency signal components or from said IIR filter.

Inventors: KARLSSON PETER, OHLSSON THOMAS, KARLSSON, PETER, OHLSSON, THOMAS
Applicants: SIEMENS ELEMA AB, SIEMENS-ELEMA AB
Application year: 1994
Main classification: A61B5
IPC codes: A61B5, H03H21, H03H17